Capacitive medical electrode

ABSTRACT

Medical electrodes in embodiments of the teachings may include one or more of the following features: (a) a metallic conductor, (b) the metallic conductor sandwiched between a first dielectric layer adjacent a top surface of the metallic conductor and a second dielectric layer located on a bottom surface of the metallic conductor, (c) a conductive gel coating on at least one of the first and second dielectric layers, (e) the metallic conductor, the dielectric layers, and the conductive gel being wrapped to form a multi-tiered electrode having a plurality of conductive surfaces, (f) an adhesive adhering the metallic conductor with the dielectric layers, (g) a tab connector to provide a connection to electrical monitoring equipment and (h) an attachment connector to provide electrical connection with a patient.

RELATED APPLICATION

This application claims priority to provisional U.S. Application Ser.No. 60/615,726, filed Oct. 4, 2004, titled Capacitive Medical Electrode,herein incorporated by reference in its entirety.

TECHNICAL FIELD

The present teachings relate generally to medical electrical sensing andstimulation devices. More particularly the present teachings relate to acapacitance electrode for sensing and reproducing electric potentials atthe surface of living tissue and introducing electrical potentials intothe tissue.

BACKGROUND

The use of electrodes for sensing electrical activity at the surface ofliving tissue, such as during the performance of anelectroencephalograph (EEG), an electromyograph (EMG), anelectrocardiograph (EKG) or a galvanic skin response (GSR) procedure iswell known. These electrodes and others are also used for stimulatingliving tissue, e.g., TENS (Transcutaneous Electric Nerve Stimulation),defibrillation, pacing (internal and external), or for transferringenergy from electrical devices to the body as in electrocautery. Theseand other prior electrodes provide resistive coupling to the testsubject, so as to facilitate the monitoring of electrical activitytherein or contain a metallic conductor in chemical contact with anelectrolytic medium.

Resistively coupled electrodes have proved to be generally suitable fortheir intended purposes, however, these electrodes do possess inherentdeficiencies, which detract from their utility. For example, resistivelycoupled electrodes can consume a lot of power, which is undesirable forbattery driven devices. Further, they can generate a substantial amountof heat, which can cause burns in defibrillation applications.

Additionally, there are limitations that may occur with both the sensingand stimulation applications using resistively coupled electrodes.Motion artifact, half-cell potential, and non-linearity or distortionsof the signal at the electrode-electrolyte interface are some of thelimitations that may occur with sensing applications. In stimulationapplications, limitations also include non-uniform current density,spikes in amplitude at the onset of the signal, and resistive powerloss. All of which are related to the electrode-patient interface.

The transmission of an electrical signal between an electrode and anionic medium involves certain capacitive and chemical issues. Currentexists in metal as a flow of electrons through the crystal lattice ofthe material. In contrast, current in an ionic solution requires themovement of cations and/or anions through the solution. The electricalinteraction between metal and an ionic solution can occur as acapacitive process, an inductive process, or as a chemical reaction.

Typically, both capacitive and chemical interactions take place duringelectrical activity between a patient and an electrode. The volume ofionic solution on a metal is called the Helmholtz double layer andcontains both the capacitive and chemical reactions. Generally allelectrodes have a capacitive component except for silver/silver chlorideelectrodes, commonly used for ECG sensing, at small currents.Additionally, platinum or other inert metals can transmit signals in apurely capacitive mode, but also at small currents only.

The nature of the reaction for most electrodes depends on multiplefactors. Generally, the metal composition of the electrode determinesthe threshold at which chemical reaction will occur, and what they willbe, presuming a saline ionic solution. Most metals, including stainlesssteel, will produce hydrogen and chlorine gases as a byproduct of thechemical reaction of the metal with the ionic solution. This isundesirable because chlorine gas can possibly irritate the patient'stissue at the anode. Further, these gases can cause corrosion of theelectrode itself.

Generally, all electrodes, except for silver/silver chloride electrodesand a few others, have a strong capacitive component. Silver/silverchloride avoids this capacitive component at small currents by “anodalchloridization of the electrode surface”. However, the silver/silverchloride electrodes create a capacitive interference with largecurrents. Electrochemical polarization of physiological electrodes is anundesirable but seemingly unavoidable phenomenon that detracts from theperformance of implanted electronic prosthetic devices. In the case ofnoble metals, polarization causes a significant waste of stimulationenergy at the electrode surface. With non-noble metals, the energy wasteis even greater and may involve electrolytic corrosion reactions. Suchcorrosion may destroy the electrode and may possibly leave toxicresidues in body tissues. The electrode-electrolyte interface presentsto a cardiac pacemaker a highly capacitive load having multiple timeconstants of the same order of magnitude as the 1- or 2-millisecond(msec) duration of a pacemaking impulse. Thus, an applied square wave ofcurrent on the electrodes does not obey Ohm's law and does not elicit asquare wave of voltage, nor is the voltage waveform a constant slope(ramp), as would be expected from a single lumped capacitor. Rather, thevoltage rises in less than a microsecond to an initial value and thenmore slowly, in at least two different time constants, until the end ofthe pulse. This capacitive interference, complicates stimulation withthis type of electrode.

It has been found that platinum electrodes can avoid toxicity since theyproduce only a small amount of chlorine. However, approximately 60% ofthe current through a platinum pacemaker electrode occurs throughcapacitance. Thus existing stimulation electrodes mostly includecapacitive effects, however, the capacitance is complex and extremelyvariable. This capacitance is undesirable for several reasons. Thecapacitance varies in a nonlinear fashion with a myriad of parametersincluding temperature and rate of change of the electrical signal comingfrom the patient. This capacitance degrades the electrical signal comingfrom the patient and is impossible to model for filtering purposes.Further, the capacitance's resistive component also degrades theelectrical signal. There are at least two ways the chemical reactionsoccurring at the electrode surface affect electrical signals. First, isthe formation of gas bubbles, which act as a physical barrier to currentpassage. Second, the half-cell potential changes with smallperturbations in the physical environment, creating electrical noise.

Purely capacitive electrodes solve this problem since they avoidchemical reactions all together, but existing technology limits theirapplications. An example of a purely capacitive electrode is dispersiveelectrodes used in electrocautery. These electrodes consist of a sheetof metal and a non-conductive adhesive gel in contact with the skin. Theadhesive gel has low conductivity but a high dielectric constant. Themetal foil forms one plate of the capacitor and the skin forms theother. The capacitance of these electrodes typically ranges in the Picofarad range. Because the electrocautery unit operates in the400-kilohertz range, the reactance is low.

Dispersive electrodes also require a low impedance interface. Resistivedispersive electrodes can monitor the adequacy of the contact betweenthe electrode and the patient's body by contact quality monitoring(“CQM”) circuitry in an electrosurgical generator. Current generatorsystems have safety circuits, which can detect when a resistiveelectrode does not have good attachment to the body. If something hascaused the electrode to be applied without adequate initial contact withthe body or some event during surgery has caused the adequate initialcontact to become inadequate, these safety circuits will detect thatproblem and terminate the current being applied.

While existing capacitive electrodes do not have the edge effect(electrical fields on the edge of the electrode) of concern forresistive type dispersive electrodes and the current transfer is muchmore uniform across the surface of the electrode compared to resistivetypes, they are not compatible with the above described CQM circuits,and thus when used do not have this protection against inadvertentmisapplication of electrocautery units used during electrosurgery. Lossydielectric designs, such as the design described in U.S. Pat. No.5,836,942, overcome this problem, but the design's resistive componentadds to unwanted heat generation. Problems faced by designers of medicalelectrodes include minimizing overall heat generation and maximizinguniformity of the current density.

Another disadvantage associated with traditional stimulating electrodes,is they often cause an initial uncomfortable shock before attaining astable sensation.

In view of the foregoing, it is desirable to provide an electrodesuitable for use in EEG, EMG, EKG, and GSR procedures and the likeovercoming the disadvantages of the prior art by manipulating theelectrode-electrolyte interface of a medical electrode in contact with abiological system and providing a large capacitance in a standard sizedelectrode. It is desirable to have a substantially capacitive electrodeto avoid chemical reactions. Additionally it is desirable to have anelectrode with a constant predictable capacitance and that can avoid ahalf-cell potential.

SUMMARY

A method of manufacturing a medical electrode in embodiments of theteachings may include one or more of the following features: (a) coatinglayers of dielectric film having a metallic conductor sandwiched betweensaid layers with a conductive gel, (b) wrapping the metallic conductorsandwiched between the layers of dielectric to form a multi-tieredelectrode having a plurality of conductive surfaces, (c) placing themulti-tiered electrode into a plastic case, (d) gluing the metallicconductor to the dielectric layers, (e) wherein the dielectric layers isa capacitive grade Mylar, (f) wherein the metallic conductor isconductive ink, (g) wherein the metallic conductor is silver, (h)wherein the plurality of conductive surfaces can be capacitively coupledto a patient, (i) wherein there is no chemical reaction between themetallic conductor and the conductive gel, and (j) wherein there is nogalvanic contact between the metallic conductor and the conductive gel.

A medical electrode according to the present teachings may include oneor more of the following features: (a) a metallic conductor, (b) a firstdielectric layer adjacent a top surface of the metallic conductor, (c) asecond dielectric layer located on a bottom surface of the metallicconductor, (d) a conductive gel coating on at least one of the first andsecond dielectric layers, (e) wherein the metallic conductor has aplurality of conductive sections, (f) wherein the conductive sectionsare in capacitive communication with adjacent sections, (g) wherein thedielectric layers are a capacitive grade Mylar, (h) wherein the metallicconductor is conductive ink, (i) wherein the metallic conductor issilver, (j) wherein the plurality of conductive sections can becapacitively coupled to a patient, (k) wherein there is no chemicalreaction between the metallic conductor and the conductive gel, and (l)wherein there is no galvanic contact between the metallic conductor andthe conductive gel.

A medical electrode according to the present teachings may include oneor more of the following features: (a) a metallic conductor, themetallic conductor sandwiched between a first dielectric layer adjacenta top surface of the metallic conductor and a second dielectric layerlocated on a bottom surface of the metallic conductor, (b) a conductivegel coating on at least one of the first and second dielectric layers,the metallic conductor, the dielectric layers, and the conductive gelbeing wrapped to form a multi-tiered electrode having a plurality ofconductive surfaces, (c) an adhesive adhering the metallic conductorwith the dielectric layers, (d) a tab connector to provide a connectionto electrical monitoring equipment, (e) an attachment connector toprovide electrical connection with a patient, (f) wherein the metallicconductor is electrochemically isolated from the patient so that thereis no galvanic interaction between them, and (g) wherein the dielectriclayers allow the transfer of electrical signals and energy to and fromthe metallic conductor and the patient.

A medical electrode according to the present teachings may include oneor more of the following features: (a) a plurality of metallicconductors, the metallic conductors sandwiched between a firstdielectric layer adjacent a top surface of the metallic conductors and asecond dielectric layer located on a bottom surface of the metallicconductors; and (b) a conductive gel coating on at least one of thefirst and second dielectric layers, the metallic conductors, thedielectric layers, and the conductive gel being layered form amulti-tiered electrode having a plurality of conductive surfaces.

A medical electrode according to the present teachings may include oneor more of the following features: (a) a plastic rim, (b) a plurality ofwire strands wrapped around the plastic rim, the wire strands spacedapart to form a plurality of conductive surfaces, and a high dielectricmaterial isolating the rim and wire strands from a patient.

BRIEF DESCRIPTION OF DRAWINGS

FIG. 1 is a side profile view of a medical electrode in an embodimentaccording to the present teachings;

FIG. 2 is a top profile view of the medical electrode shown in FIG. 1 inan embodiment according to the present teachings;

FIG. 2A is a top profile view of a medical electrode in an embodimentaccording to the present teachings;

FIG. 2B is a top profile view of a medical electrode in an embodimentaccording to the present teachings;

FIG. 3 is a side profile view of a multi-tiered medical electrode in anembodiment according to the present teachings;

FIG. 4 is a side profile view of a multi-tiered medical electrode in anembodiment according to the present teachings;

FIG. 4A is an overhead profile view of a multi-tiered medical electrodein an embodiment according to the present teachings;

FIG. 5 is a overhead profile view of a TENS medical electrode in anembodiment according to the present teachings;

FIG. 5A is an side profile view of a TENS medical electrode in anembodiment according to the present teachings;

FIG. 6 is an overhead profile view of a dispersive medical electrode inan embodiment according to the present teachings;

FIG. 6A is a side profile view of a dispersive medical electrode in anembodiment according to the present teachings;

FIG. 7 is an overhead profile view of an implanted pacing/defibrillationmedical electrode in an embodiment according to the present teachings;

FIG. 8 is a frequency response curve representation taken from a medicalelectrode in an embodiment according to the present teachings;

FIG. 9 is a circuit diagram model of a medical electrode in anembodiment according to the present teachings.

FIG. 10 is a side profile view of a medical electrode in an embodimentaccording to the present teachings;

FIG. 11 is a top profile view of a medical electrode in an embodimentaccording to the present teachings;

FIG. 12 is a side profile view of a medical electrode in an embodimentaccording to the present teachings; and

FIG. 13 is a top profile view of a medical electrode in an embodimentaccording to the present teachings.

DETAILED DESCRIPTION

The following discussion is presented to enable a person skilled in theart to make and use the present teachings. Various modifications to theillustrated embodiments will be readily apparent to those skilled in theart, and the generic principles herein may be applied to otherembodiments and applications without departing from the presentteachings. Thus, the present teachings are not intended to be limited toembodiments shown, but are to be accorded the widest scope consistentwith the principles and features disclosed herein. The followingdetailed description is to be read with reference to the figures, inwhich like elements in different figures have like reference numerals.The figures, which are not necessarily to scale, depict selectedembodiments and are not intended to limit the scope of the presentteachings. Skilled artisans will recognize the examples provided hereinhave many useful alternatives and fall within the scope of the presentteachings.

With reference to FIG. 1, a side profile view of a medical electrode inan embodiment according to the present teachings is shown. Electrode 10can include an upper dielectric layer 12 and a lower dielectric layer 14and a conductive metal 16 sandwiched between layers 12 and 14. Layers 12and 14 can be held together with a thin layer of adhesive 18. Dielectriclayers 12 and 14 can be made of a capacitive grade Mylar, however it iscontemplated that layers 12 and 14 could be made of most any dielectricmaterial such as cellophane, cellulose, acetate resin, Neoprene, orpolyvinylchloride, for example without departing from the spirit of theteachings. Further, conductive metal 16 can be comprised of silver ink,however, conductive metal 16 can be comprised of most any conductivematerial such as carbon, gold, platinum, copper, or stainless steel, forexample without departing from the spirit of the teachings. Asillustrated adhesive 18 can be a pressure sensitive biocompatible glue,however, most any type of adhesive could be used such as polyurethane,hot melt, or aqueous adhesive emulsion, for example without departingfrom the spirit of the teachings. As illustrated, electrode 10 can becomprised of layers 12 and 14 having a thickness of about 0.5 mil,conductor 16 with a thickness of about 0.30 Mil, and adhesive layer 18with a thickness or about 0.43 mil.

With reference to FIG. 2, a top profile view of the medical electrodeshown in FIG. 1 in an embodiment according to the present teachings isshown. When layers 12 and 14 are adhered together with adhesive 18sandwiching conductor 16, electrode 10 appears in the form of strip 20.Strip 20 may then be coated with a conductive gel 22 (FIG. 3). Coatinggel 22 can be comprised of a conducting hydrogel, however, conductivegel 22 can be most any type of conductive substance, such as standardmedical electrode gels, for example without departing from the spirit ofthe teachings. Gel 22 can be applied to both layer 12 and 14. Strip 20can be lengthened to achieve a higher capacitance, shortened to achievea lower capacitance, and manufactured to a specific length to achieve adesired capacitance. Sections 40 are chosen for their size in that theyhave approximately the same surface area as a standard medicalelectrode. Further, sections 40 are chosen by the size of capacitancethey will have. For example, each section 40 can be 1.5 inches in lengthand can have a capacitance of 7 nanofarads. Therefore a strip of tensections 40 would achieve a total capacitance of approximately 70nanofarads, which has been found to perform well. By knowing thecapacitance of each section 40 of strip 20, it is relatively easy tocustom manufacture electrodes based upon the need of the user. Further,it is not necessary for section 40 to have a square shape. As shown inFIG. 2A, electrode 10 can have sections 40 with a circular shape. FIG.2B shows an electrode 10 having sections 40 with a rectangular shape.The shapes can be chosen depending on the application electrode 10 willbe used for and/or which shape provides the desired capacitance.Conductive metal 16 can be solid with holes 32, however, conductivemetal can also be a mesh, wire frame, or segmented without departingfrom the spirit of the invention.

With reference to FIG. 3, a side profile view of a multi-tiered medicalelectrode in an embodiment according to the present teachings is shown.After conductive gel 22 is applied, strip 20 can be rolled or foldedsection 40 over section 40 from distal end 28 to proximal end 30 into athree-dimensional structure 24 to insure all surfaces of strip 20 are inelectrical communication with a biological system 34, such as a patientas will be described in more detail below. After strip 20 is rolled intomulti-tiered structure 24, multi-tiered structure 24 can be placed intoplastic case 38, which holds electrode 10 into a tightly wound or foldedmulti-tiered structure 24. A tab connector 26 can be provided atproximal end 30 to provide a connection to electrical monitoringequipment (not shown), such as an EEG, an EMG, or an ECG, for example.Adhesive 18 and gel 22 are not applied to tab 26 so an externalconnector (not shown) can be applied to conductor 16. Holes 32 can belocated in electrode 10 to facilitate conduction of an electrical signalto and from skin or tissue 34. Holes 32 allow for conduction of anelectrical signal from the upper layers of structure 24 through gel 22to the patient. Each hole 32 can extend completely through strip 20.There is approximately a 2 mm strip around hole 32 where there is nosilver ink coated on strip 20. Holes 32 allow the current to travel downthrough structure 24. Without holes 32 all of the current would travelalong the outer edge of electrode 10 except for the portion of strip 20closest to the patient's skin. Thus holes 32 shorten the current path tothe patient considerably and thus decrease the resistance of electrode10. It's also of note that conducting gel 22 overlaps the outer edge ofelectrode 10 providing another path to the patient. As illustrated,holes 32 are placed at regular intervals. By having holes 32 at regularintervals the conductive path from the upper layers to the skin can beshortened. However, it is fully contemplated holes 32 can be atirregular intervals and randomly placed without departing from thespirit of the present teachings.

The present teachings overcome the disadvantages associated with someprior art systems by manipulating the electrode-electrolyte interface ofmedical electrode 10 in contact with biological system 34. As discussedabove, one embodiment of the present teachings provides conductor 16,which can be isolated from gel 22 so there is no galvanic contactbetween gel 22 and conductor 16, though not excluding galvanic contactwith other components of the system, such as layer 14. The dielectricproperties of layers 12 and 14 not only prevent any galvanic contactbetween gel 22 and conductor 16, but also allows for the transfer ofelectrical signals and energy to and from conductor 16. Further, layers12 and 14 eliminate any chemical interactions between gel 22 andelectrode 10. The folded or rolled structure 24 also maximizes thesurface area of electrode 10 through its multi-tiered structure 24. Thefunction of structure 24 is to allow a large capacitance in a standardsized electrode through multi-tiered conductor 24, which provides alarge capacitance when connected to an A/C power source.

As stated above, the variables of note in an electrode design are theuniformity of the current density, the impedance, and (for internalelectrodes) the toxicity. Purely capacitive electrode 10 provides a morebiocompatible surface and also eliminates any oxidation-reductionreactions at interface 36. Oxidation or reduction reactions at theelectrode-electrolyte interface 36 set up an electrical potential, whichcan be measured, called a half-cell potential. Half-cell potential issensitive to physical perturbations in the environment. The fluctuationsin half-cell potential constitute an alternating current that istransmitted through patient electrode interface 36 creating a noisysignal. By eliminating half-cell potential, one source of motionartifact can be eliminated. It is of note that even in platinumelectrodes monitoring small signals, the half-cell potential producesnoise, even though the system is perfectly polarized. Since layers 12and 14 are sandwiched between conductor 16 and gel 22, there is nochemical reaction to affect the capacitance of electrode 10. Therefore,since the capacitance is fixed in electrode 10 and does not vary withsurface and signal characteristics, there are minimal motion artifactresults. Further, electrode 10 and skin 34 are in series with theresistance of whatever monitor is connected to electrode 10. Thisconstitutes an RC circuit, which can be tuned to a particular frequencyband. Thus the electrical signals of a patient can be more efficientlymonitored without distortion or loss.

With reference to FIGS. 4 & 4A, a side and top profile view of amulti-tiered medical electrode in an embodiment according to the presentteachings is shown respectively. Electrode 10 can be oriented so that acentral axis 50 of electrode 10 is perpendicular to skin 34 in a“jellyroll” configuration. This orientation provides a more uniformcurrent density since all layers contribute equally. As can be seen fromFIG. 4A, strip 20 is rolled in contrast to strip 20 shown in FIG. 3,which is folded. After strip 20 is rolled it can be placed in a case 52and then attached to a base plate 54, which is made of an insulationmaterial. Base plate 54 is utilized to stabilize electrode 10 as it sitsupon the patient's skin 34. Without base plate 54, electrode 10 wouldhave trouble remaining upright and would easily fall over and roll offof the patient.

With reference to FIGS. 5 & 5A, a top and side profile view of a TENSmedical electrode in an embodiment according to the present teachings isshown respectively. A TENS electrode 60 consists of wire mesh 62 wrappedaround plastic rim 66 and insulated with a high dielectric material 64which is biocompatible and inert such as Formvar enamel. This wire meshdesign provides for a robust electrode lending itself to use as animplantable electrode, which would be in direct contact with body fluidsinstead of a conducting gel. As illustrated, dielectric material 64 ismade of Formvar enamel, however it is contemplated material 64 could bemade of most any dielectric material such as glass or polyvinylchloride,for example without departing from the spirit of the teachings. In thisapplication, wire mesh 62 provides the purely capacitive multi-tieredcomponent. The purely capacitive component is created by the multiplecapacitances in-between each strand 68 of wire mesh 62. Wire mesh 62 canbe made of copper, however, wire mesh 62 can be made of most anyconductive metal such as gold, platinum, silver, or stainless steel, forexample, without departing from the spirit of the teachings. Similar tomulti-tiered structure 24 discussed above, electrode 60 is tieredhorizontally to a patient's skin to provide the capacitive componentsimilar to the electrode structure of FIGS. 4 and 4A. The distancebetween wire lengths determines the electrical communication with anelectrolytic medium and determines the capacitive value of electrode 60.It's helpful if strands 68 don't come in contact with each other thuspossibly decreasing the effective surface area. A randomly woundstructure could be utilized, however, the inventors have discovered thisstructure performed inferiorly when compared to the structure shown inFIG. 5 due to the wire insulation possibly cracking when randomlycompressed. The structure of the electrode varies with the application.While the basic design is a wire mesh, the shape of the rim and thenumber of layers can be varied, for example, without departing from thespirit of the invention. As illustrated in FIG. 7, one variation withouta rim provides flexibility for insertion. Other variations include abraided structure, such as a “rope” electrode.

In contrast to prior electrodes, the present teaching discloseselectrode 60 has even lower impedance than previous capacitiveelectrodes. In the present teachings, the relatively high capacitanceminimizes or lowers the significance of the reactance. Present TENSelectrodes sometimes use high resistance materials such as carbonizedrubber in order to achieve uniform current density. This resistance isundesirable as discussed above. A capacitive electrode with lowimpedance would provide a uniform current density unlike a resistiveelectrode. The lower impedance, which occurs as reactance, results inlower power consumption than resistive electrodes discussed above. Thisproves to be especially useful when electrode 60 is being used inapplications utilizing batteries by greatly prolonging battery life.

FIGS. 6 and 6A is a side and top profile view of a dispersive medicalelectrode in embodiments according to the present teachings is shownrespectively. The structure of dispersive electrode 70 minimizes overallheat generation and maximizes uniformity of the current density.Electrode 70 provides very low impedance, a large part of which isreactance. Electrode 70 can have a first grid 72 and a second grid 74which are isolated from each other. Grids 72 & 74 rest upon and areattached to insulated backing 76 comprised of Latex material, however,most any type of insulative material could be utilized without departingfrom the spirit of the teachings. A gel 78, such as discussed above isthen applied to the grids 72 and 74. Grids 72 & 74 are comprised ofcopper, however, grids 72 & 74 can be comprised of most any conductivemetal such as gold, platinum, silver, or stainless steel, for example,without departing from the spirit of the teachings. While electrode 70capacitive electrode, it allows for use of the safety mechanisms ofelectrocautery units, such as the contact quality monitoring (CQM)system. This system monitors contact with a patient's skin by comparingthe impedance between grids 72 & 74. If the electrode contact iscompromised, the CQM disables the electrocautery, thus preventing burns.One could also employ Mylar strip electrodes in a similar manner.

With reference to FIG. 7, an overhead profile view of an implantedpacing/defibrillation medical electrode in an embodiment according tothe present teachings is shown. Pacing/defibrillation electrode 80consists of a length of steel wire 82, formed in a spiral. Electrode 80can be formed of steel wire 82; however, electrode 80 can be formed ofmost any conductive metal such as gold, platinum, copper, or stainlesssteel, for example, without departing from the spirit of the teachings.Electrode 80 would, similar to the other electrodes discussed above, becoated with a material, which has a good biocompatibility and a highdielectric constant. The biocompatibility would allow for insertion intoa patient and the dielectric would allow for electrical contact betweenthe patient and wire 82 while preventing any chemical reaction betweenwire 82 and the patient. Electrode 80 could be straightened and threadedinto a hollow catheter for insertion. Once the tip of the catheter wasattached to the endocardium, the catheter would be removed and theelectrode would assume a predetermined shape such as a spiral.

Pacing/defibrillation electrode 80 provides another embodiment where thetechnology of the present teachings would improve existing electrodes.Present pacing/defibrillation leads sacrifice uniformity of currentdensity for low impedance. Capacitive leads have an inherently bettercurrent uniformity as discussed above.

With reference to FIG. 8, a frequency response curve representationtaken from a medical electrode in an embodiment according to the presentteachings is shown. One skilled in the art can readily see theelectrodes of the present teachings function as an RC circuit whenapplied to the patient and connected to a monitor. FIG. 8, showsconductivity versus frequency for a wire electrode. As can be seen thereis no shift in phase angle over the selected range of an electrode pairaccording to the present teachings. There is a frequency range wherethere is little loss of signal, but a drop off at both the high and lowends. The plot of FIG. 8 shows that the capacitance of the electrode ofthe present teachings is predictable.

With reference to FIG. 9, a circuit diagram model of a medical electrodein an embodiment according to the present teachings is shown.Experimental data verifies the circuit diagram in FIG. 9 as a model fora medical electrode in accordance with the present teachings. Using thiscircuit diagram allows calculation of the parameters required for agiven frequency range. The lower cutoff is determined by thecapacitance; the higher the capacitance, the lower the cutoff frequency.Likewise, the resistance of the monitor determines the upper limit, thehigher the viewing resister, and the higher the cutoff. With a standard10M-ohm resister, the frequency is very high. This can be adjusted,however.

With reference to FIGS. 10 and 11, profile views of a medical electrodein embodiments according to the present teachings are shown. Theinventors have found that by adding inductance to capacitive electrode100, fine tuning of electrode 100 can be achieved. A purely capacitiveelectrode will transmit a square wave as a ramp, with a subsequent decayto baseline similar to a saw tooth waveform. Inductance can balance thistendency and can allow the transmission of a square wave into the tissueessentially unchanged. The added inductance can be achieved by providingconcentric rings 102 of ferrous in a layer of gel 104, which is incontact with the skin. Rings 102 are insulated from the electrolytesolution of gel 104 by an inert material 106. Alternatively a number oftiny rings could be randomly imbedded the gel with the ringsperpendicular to the flow of current.

With reference to FIG. 12, a side profile of a medical electrode in someembodiments according to the present teachings is shown. By adding tinyspheres 202 of ferric material, which have been coated with insulation,into electrode 200 inductance can affect both the current in the silverink and the current in gel 204. Alternatively, an inductance circuit 206can be placed in series with electrode 200 to provide inductance forfine tuning. Circuit 206 could be placed at the tab on electrode 200 orin the circuitry of source 208.

With reference to FIG. 13, a top profile view of a medical electrode inan embodiment according to the present teachings is shown. In thisembodiment, a layer 300 is added between electrode 10 and the patientthat would focus or direct an electric signal. Layer 300 would consistof an insulating sheet with a hole 302. Insulating sheet 300 would haveadhesive to attach to the skin. Current would be forced through hole302. This would allow the signal to be more localized. The current bynecessity transverses only the aperture, rather than the entire contactsurface as it would without the added layer.

One skilled in the art will appreciate the present teachings can bepracticed with embodiments other than those disclosed. The disclosedembodiments are presented for purposes of illustration and notlimitation, and the present teachings are limited only by the claimsfollow.

1. A method of manufacturing a medical electrode, comprising: coatinglayers of dielectric film having a metallic conductor sandwiched betweensaid layers with a conductive gel; and wrapping the metallic conductorsandwiched between the layers of dielectric to form a multi-tieredelectrode having a plurality of conductive surfaces.
 2. The method ofclaim 1, further comprising the step of placing the multi-tieredelectrode into a plastic case.
 3. The method of claim 1, furthercomprising the step of gluing the metallic conductor to the dielectriclayers.
 4. The method of claim 1, wherein the dielectric layers is acapacitive grade Mylar.
 5. The method of claim 1, wherein the metallicconductor is conductive ink.
 6. The method of claim 5, wherein themetallic conductor is silver.
 7. The method of claim 1, wherein theplurality of conductive surfaces can be capacitively coupled to apatient.
 8. The method of claim 1, wherein there is no chemical reactionbetween the metallic conductor and the conductive gel.
 9. The method ofclaim 1, wherein there is no galvanic contact between the metallicconductor and the conductive gel.
 10. A medical electrode, comprising: ametallic conductor; a first dielectric layer adjacent a top surface ofthe metallic conductor; a second dielectric layer located on a bottomsurface of the metallic conductor; and a conductive gel coating on atleast one of the first and second dielectric layers.
 11. The medicalelectrode of claim 10, wherein the metallic conductor has a plurality ofconductive sections.
 12. The medical electrode of claim 11, wherein theconductive sections are in capacitive communication with adjacentsections.
 13. The medical electrode of claim 10, wherein the dielectriclayers are a capacitive grade Mylar.
 14. The medical electrode of claim10, wherein the metallic conductor is conductive ink.
 15. The medicalelectrode of claim 14, wherein the metallic conductor is silver.
 16. Themedical electrode of claim 10, wherein the plurality of conductivesections can be capacitively coupled to a patient.
 17. The medicalelectrode of claim 10, wherein there is no chemical reaction between themetallic conductor and the conductive gel.
 18. The medical electrode ofclaim 10, wherein there is no galvanic contact between the metallicconductor and the conductive gel.
 19. A medical electrode, comprising: ametallic conductor, the metallic conductor sandwiched between a firstdielectric layer adjacent a top surface of the metallic conductor and asecond dielectric layer located on a bottom surface of the metallicconductor; and a conductive gel coating on at least one of the first andsecond dielectric layers, the metallic conductor, the dielectric layers,and the conductive gel being wrapped to form a multi-tiered electrodehaving a plurality of conductive surfaces.
 20. The medical electrode ofclaim 19, further comprising an adhesive adhering the metallic conductorwith the dielectric layers.